US9498625B2 - Hemodynamic performance enhancement through asymptomatic diaphragm stimulation - Google Patents

Hemodynamic performance enhancement through asymptomatic diaphragm stimulation Download PDF

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US9498625B2
US9498625B2 US14/107,976 US201314107976A US9498625B2 US 9498625 B2 US9498625 B2 US 9498625B2 US 201314107976 A US201314107976 A US 201314107976A US 9498625 B2 US9498625 B2 US 9498625B2
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electrical
diaphragm
cardiac
stimulation
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US20140172040A1 (en
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Peter T. Bauer
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Viscardia Inc
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Viscardia Inc
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Publication of US20140172040A1 publication Critical patent/US20140172040A1/en
Assigned to VISCARDIA, INC. reassignment VISCARDIA, INC. STOCK PURCHASE AND CONTRIBUTION AGREEMENT Assignors: INOVISE MEDICAL, INC.
Priority to US15/273,643 priority patent/US9694185B2/en
Priority to US15/288,130 priority patent/US10335592B2/en
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Priority to US15/612,690 priority patent/US9968786B2/en
Priority to US15/950,774 priority patent/US10315035B2/en
Priority to US16/395,970 priority patent/US11020596B2/en
Priority to US16/399,896 priority patent/US11147968B2/en
Priority to US17/243,341 priority patent/US11684783B2/en
Priority to US17/477,432 priority patent/US11666757B2/en
Priority to US18/137,982 priority patent/US12364859B2/en
Priority to US18/196,148 priority patent/US12144993B2/en
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/3601—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation of respiratory organs
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording for evaluating the cardiovascular system, e.g. pulse, heart rate, blood pressure or blood flow
    • A61B5/024—Measuring pulse rate or heart rate
    • A61B5/02438—Measuring pulse rate or heart rate with portable devices, e.g. worn by the patient
    • A61B5/0452—
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    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/103—Measuring devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
    • A61B5/11—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor or mobility of a limb
    • A61B5/113—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor or mobility of a limb occurring during breathing
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
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    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/316—Modalities, i.e. specific diagnostic methods
    • A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
    • A61B5/346—Analysis of electrocardiograms
    • A61B5/349—Detecting specific parameters of the electrocardiograph cycle
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    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/316—Modalities, i.e. specific diagnostic methods
    • A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
    • A61B5/346—Analysis of electrocardiograms
    • A61B5/349—Detecting specific parameters of the electrocardiograph cycle
    • A61B5/352—Detecting R peaks, e.g. for synchronising diagnostic apparatus; Estimating R-R interval
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    • A—HUMAN NECESSITIES
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    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6846—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
    • A61B5/6847—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive mounted on an invasive device
    • A61B5/686—Permanently implanted devices, e.g. pacemakers, other stimulators, biochips
    • A—HUMAN NECESSITIES
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    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6846—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
    • A61B5/6867—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive specially adapted to be attached or implanted in a specific body part
    • A—HUMAN NECESSITIES
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    • A61B5/7203—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal
    • A61B5/7207—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal of noise induced by motion artifacts
    • A61B5/721—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal of noise induced by motion artifacts using a separate sensor to detect motion or using motion information derived from signals other than the physiological signal to be measured
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    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/362—Heart stimulators
    • A61N1/3627—Heart stimulators for treating a mechanical deficiency of the heart, e.g. congestive heart failure or cardiomyopathy
    • A—HUMAN NECESSITIES
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    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/362—Heart stimulators
    • A61N1/365—Heart stimulators controlled by a physiological parameter, e.g. heart potential
    • A61N1/36585—Heart stimulators controlled by a physiological parameter, e.g. heart potential controlled by two or more physical parameters
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    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/06—Arrangements of multiple sensors of different types
    • A61B2562/063—Arrangements of multiple sensors of different types in a linear array

Definitions

  • the present invention pertains to an implantable medical system, and to an associated methodology, employing, and managed by electrical circuit structure, which features logic-including, internal-control circuitry referred to herein as computer structure, or more simply as a computer, for enhancing hemodynamic performance in subjects with cardiac disease through applying carefully timed, regular, per-cardiac-cycle, synchronized, asymptomatic, electrical pulsed stimulation to the diaphragm intended to induce short-term occurrences of biphasic diaphragmatic motion.
  • electrical circuit structure which features logic-including, internal-control circuitry referred to herein as computer structure, or more simply as a computer, for enhancing hemodynamic performance in subjects with cardiac disease through applying carefully timed, regular, per-cardiac-cycle, synchronized, asymptomatic, electrical pulsed stimulation to the diaphragm intended to induce short-term occurrences of biphasic diaphragmatic motion.
  • control circuitry which forms part of what is referred to as electrical circuit structure
  • the system preferably additionally permits, in a modified form, selective, remote-telemetry-implemented communication from outside the anatomy to allow for other kinds of system-behavioral adjustments, such as ones that relate to timing matters.
  • the term “hemodynamic performance” is used synonymously herein with the terms “cardiovascular performance” and “cardiac function”.
  • the biphasic diaphragmatic motion produced by electrical stimulation is what is called herein caudal-followed-by-cranial motion of the diaphragm.
  • the included “computer-structure” logic componentry which may be hard-wired to perform its intended functions, or more preferably fully or partially programmable, as by telemetry, may also feature an appropriate microprocessor. It may also include, or be appropriately internally associated with, a suitable “state machine” for implementing various important timing controls, as will be explained below.
  • Pulsed stimulation of the type just above mentioned, properly characterized and applied triggers, in each case, a very short (only a few tens of milliseconds) pulse-like, biphasic (singular-caudal-followed-by-singular-cranial) motion of the diaphragm, and, relatedly also, a substantially following pumping-relevant motion of the left ventricle in the heart which rests on the diaphragm.
  • This stimulation creates this motion-generating activity in a manner which, when properly and synchronously timed in relation to the onset of left-ventricular contraction, improves hemodynamic performance through enhancing the important cardiac pumping functions of both (a) late diastolic filling, and (b) early systolic contraction.
  • Asymptomatic stimulation implemented in the practice of the present invention is also referred to herein as PIDS stimulation—the acronym PIDS standing for the phrase “pacing induced diaphragmatic stimulation”.
  • PIDS stimulation the acronym PIDS standing for the phrase “pacing induced diaphragmatic stimulation”.
  • systemic and methodologic are (1) that sensing of what is referred to herein as a valid electrical or mechanical V-event, and (2) that related, sensing-based, ultimate applying of electrical stimulation to the diaphragm, take place, with the system installed for use with a subject, from an implanted systemic disposition directly adjacent, and preferably in contact with, a selected surface region in the subject's diaphragm.
  • this selected surface region which may be either an inferior (preferred), or a superior, surface region in the diaphragm, and which may be chosen to be at many different, diaphragmatic surface locations, is disposed left-lateral relative to the subject's anatomy—and under all circumstances, out of contact with the heart.
  • a V-event in either category (electrical or mechanical), is defined herein as being either the onset of left-ventricular contraction, or a cardiac electrical or mechanical event having a predictably known relationship to such an onset.
  • a valid electrical V-event is treated as being either the electrical R or Q wave, and a valid mechanical V-event is treated as being the S1 heart sound.
  • Cardiac-cycle-by-cardiac-cycle, synchronized, diaphragmatic stimulation is timed, selectively in different ways—anticipatory (early), or following (late)—in relation to per-cardiac-cycle, detected, valid V-events.
  • systemic and methodologic is the effective incorporation in the proposed system and associated methodology of a focus, through the use of a system-included accelerometer, preferably multi-axial in character, and even more preferably three-dimensional in nature, on the monitoring and recording of the mechanical waveform of per-cardiac-cycle, mechanical diaphragmatic biphasic motion which is actually produced by applied, electrical diaphragmatic stimulation in comparison with a pre-set, diaphragmatic-motion reference waveform.
  • a system-included accelerometer preferably multi-axial in character, and even more preferably three-dimensional in nature
  • Stimulation-induced diaphragmatic movements are, in relation to normal respiration-motion frequency (typically about 0.2-0.3-Hz), and as mentioned, short-term, relatively high-frequency (typically about 12-15-Hz), pulse-like motions. These quick motions are superimposed on the regular, and much lower frequency, diaphragmatic respiration movements.
  • the initial, short-term caudal movement effected by diaphragmatic stimulation pulls on the left ventricle, and if well timed, such stimulation-resulting “pulling” increases the atrial contribution to left-ventricular filling during late diastole (i.e., a so-called “atrial kick”) with a resulting subsequent increase in stroke volume via the recognized, Frank-Starling mechanism.
  • the secondary, stimulation-induced movement of the diaphragm which is cranial, and which is also much faster than regular diaphragmatic respiratory motion, causes the left ventricle to be “kicked” upwardly, and If this secondary movement occurs in the early part of systole, and prior to the closure of the mitral valve, it enhances cardiac function further by increasing the momentum of ventricular contraction.
  • a system including (a) bi-modal (cardiac-electrical-activity sensing in one mode, and related diaphragmatic electrical stimulating in the other mode) electrode structure operatively connectable to a selected surface region in a subject's diaphragm, and (b) monitoring and controlling circuit structure which is connected to the electrode structure, and operable (1) to receive and process electrode-structure-sensed electrical cardiac activity when the electrode structure, under the influence of the circuit structure, is functioning in its sensing mode, and (2), based on such receiving and processing, to communicate to the diaphragm via the electrode structure, when the latter is functioning, also under the influence of the circuit structure, in its stimulating mode, appropriate diaphragmatic stimulation.
  • the selected, diaphragmatic surface region is disposed (1) preferably, but not necessarily, at a location which is lateral, and even more specifically left-lateral, within a subject's anatomy, and (2) in all instances out of contact with, the subject's heart
  • the mentioned circuit structure includes computer structure which specifically operates, relative to the circuit structure's delivery of electrical stimulation through the electrode structure, to control appropriately predetermined timed relationships relative to noted presences, in received and monitored cardiac-cycle electrical-activity information, of valid electrical V-events.
  • contemplated in the practice of the invention are two, different categories of such predetermined timed, or timing, relationships, one of which involves anticipation of a next-expected, valid, cardiac-cycle, electrical V-event, and the other of which involves a following of the last-sensed, valid, cardiac-cycle, electrical V-event.
  • timing relationships are equally applicable to another form of the system of the invention, discussed below, which further includes an accelerometer (single or plural-axis), also referred to herein as a mechanical sensing structure, that is designed to detect heart sounds, and in particular S1 heart sounds, as valid mechanical V-events.
  • an augmented form (the “another form” of the invention mentioned immediately above) of this just-presented description of the invention is one in which the proposed system further includes specifically a three-dimensional accelerometer (called also a mechanical sensing structure), (a) disposed adjacent, and operatively associated with, the electrode structure for contact-associated disposition in a motion-sensing relationship with, and with respect to, the subject's diaphragm, (b) operatively connected to the mentioned circuit structure, and (c) constructed to be responsive to any motion produced in the subject's diaphragm as a consequence of electrical diaphragmatic stimulation, and in relation to such responsiveness, to generate and communicate to the circuit structure a diaphragmatic-motion confirmation signal possessing a waveform which is directly indicative of such motion.
  • a three-dimensional accelerometer called also a mechanical sensing structure
  • the circuit structure's included computer structure features a waveform monitoring and recording substructure for comparing the waveform of a communicated confirmation signal with a reference waveform, and recording the conformation-signal waveform for subsequent review.
  • an included accelerometer functions, additionally, for sensing, in a subject's cardiac cycles, cardiac-cycle, S1 heart-sound, mechanical activity—a valid mechanical V-event—which is discernible at the selected, diaphragmatic surface region, and that (b), the included circuit structure receives this mechanical valid V-event information from the accelerometer, and is operable, in predetermined timed relationships to noted presences, in such received mechanical S1-heart-sound, of valid V-event information, to deliver asymptomatic electrical stimulation through the electrode structure to the subject's diaphragm for the purpose of triggering the intended biphasic, caudal-followed-by-cranial, motion of the diaphragm.
  • a further modified form of the basic system of the invention contemplated for implementation in certain applications, and representationally pictured, described and included herein in each of the two principal embodiments disclosed, is one wherein the computer structure which forms part of the included circuit structure possesses timing-adjustment substructure capable of making an adjustment periodically in the predetermined timed relationship which determines when, in relation to a sensed, valid V-event, electrical diaphragmatic stimulation occurs.
  • This modification is versatile in its utility, offering the possibility of adjusting, either remotely, or internally automatically if desired, such stimulation timing in a manner aimed at further enhancing a subject's hemodynamic performance if, and as, the subject's heart-behavior conditions change over time.
  • the invention offers a method for improving the hemodynamic performance of a subject's heart including, from adjacent a selected surface region in the subject's diaphragm which is out of contact with, the heart, (1) sensing and noting the presences in the subject's cardiac cycles of a selected one of (a) per-cycle valid electrical, and (b) per-cycle valid mechanical, V-events, (2) based upon such sensing, and upon noting each of such selected, V-event presences, applying, in a predetermined timed relationship to such a noting, associated, asymptomatic electrical stimulation directly to the diaphragm, preferably at the selected diaphragmatic surface region, for the purpose of triggering biphasic, caudal-followed-by-cranial motion of the diaphragm, (3) following the applying step, monitoring the waveform of resulting diaphragmatic motion, (4) after performing the monitoring step, comparing the monitored diaphragmatic-motion waveform with a reference, dia
  • the invention methodology further includes (1) choosing the selected diaphragmatic surface region to be on one of (a) the inferior, and (b) the superior, side of the diaphragm, and (2) choosing the selected, per-cycle valid V-event whereby, if it is to be electrical, it is one of (a) the R wave, and (b) the Q wave, and if mechanical, it is the S1 heart sound.
  • FIG. 1 is an isometric, electrode-side, facial view of a fully implantable fully self-contained, self-powered, singular capsule-form embodiment of the system of the present invention.
  • FIG. 2 is a same-scale, lateral isometric view of the embodiment shown in FIG. 1 , slightly rotated about two axes relative to what is seen in FIG. 1 .
  • FIG. 3 is a plan view of the invention embodiment shown in FIGS. 1 and 2 , drawn on about the same scale used in these two figures, and pictured with the body of the capsule in this embodiment opened to show internally contained electrical circuitry, an accelerometer, and an included battery.
  • FIG. 4 which uses the same drawing scale as that seen in FIG. 3 , is a lateral cross section taken generally from the lower side of FIG. 3 .
  • FIG. 5 is a basic block/schematic diagram illustrating electrical and mechanical componentry employed in the system of the invention and incorporated both in the invention embodiment pictured in FIGS. 1-4 , inclusive, and in the still-to-be-mentioned, alternative embodiment shown in FIG. 8 .
  • FIG. 6A is a frontal view of an internal portion of a subject's anatomy illustrating preferred, implanted positioning therein proposed for the system embodiment shown in FIGS. 1-4 , inclusive.
  • FIG. 6B is similar to, and is drawn on about the same scale as that employed in, FIG. 6A , except that it shows an alternative placement in the anatomy for the system of FIGS. 1-4 , inclusive.
  • FIGS. 7A, 7B present enlarged-scale, fragmentary portions of the anatomical structure shown in FIGS. 6A, 6B , with the system of FIGS. 1-4 , inclusive, removed for clarity purposes, illustrating, specifically, biphasic mechanical movement, or motion, of the heart resulting from electrical stimulation, and resulting mechanical motion, of the diaphragm and heart in accordance with practice of the methodology of the present invention.
  • FIG. 7A pictures a condition of asymptomatic-stimulation-produced caudal diaphragmatic motion
  • FIG. 7B a condition of related, immediate-time-following, cranial diaphragmatic motion.
  • FIG. 8 illustrates an alternative, fully implantable systemic embodiment of the present invention—one which has a distributed structural characteristic resulting from the condition that certain components in this embodiment are arranged in two assemblies that are separated from one another by an interconnecting communication lead structure.
  • FIGS. 9A, 9B are similar to FIGS. 6A, 6B , respectively, differing in that they illustrate two, alternative, proposed internal anatomical placements for certain ones of the components included in the embodiment of the invention pictured in FIG. 8 .
  • FIGS. 6A, 6B, 9A and 9B the exposed anatomical contents are greatly simplified in order to avoid unnecessary complexity without compromising disclosure necessity, and in this context, lower portions of the left-side phrenic nerve structure have been removed to afford better viewing clearance to see the positioning illustrated therein for implanted system structure.
  • FIGS. 1-7B inclusive, and in FIGS. 9A and 9B , and the several moved anatomical positions, and changed anatomical configurations, pictured in FIGS. 7A and 7B , are not necessarily drawn to scale.
  • FIGS. 10 and 11 present two, different, laddergram illustrations picturing, respectively, what are referred to herein as early diaphragmatic, and late diaphragmatic, electrical stimulation.
  • FIG. 12 is a two-trace, common-time-base, graphical presentation relating to electrical V-event sensing, associated cardiac-cycle-synchronized, diaphragmatic stimulation, and resulting diaphragmatic and left-ventricle biphasic mechanical motions.
  • FIG. 13 furnishes an enlarged view of a single cardio cycle event pictured between a pair of spaced, vertical, short dashed lines in FIG. 12 .
  • FIG. 14 is a high-level, block/schematic diagram illustrating both the basic, and one modified, form of the architecture of the methodology of the present invention.
  • FIGS. 1-5 indicated generally at 20 is one preferred form of a self-contained, self-powered, fully implantable medical system constructed in accordance with the present invention for improving the hemodynamic performance of a subject's heart.
  • System 20 accomplishes such improvement, as will be explained, through applying specially timed, cardiac-cycle-synchronized, asymptomatic, electrical stimulation directly to the subject's diaphragm to produce very short duration, relatively high-frequency (as mentioned above), bi-phasic motion of the diaphragm, which motion becomes communicated/applied directly to the underside of the left ventricle in the heart to create, essentially, a diaphragmatic-motion-following, bi-phasic “pumping” motion in and for the underside of, and thus within, the left-ventricle.
  • System 20 as seen in FIGS. 1-4 , inclusive, has what is referred to herein as a singular capsule form 22 .
  • This form features a small, easily implantable, elongate, thin, non-electrically-conductive, and appropriately biocompatible capsule body, or capsule, 24 having the shape shown, with a length herein of about 1.25-inches, a width of about 0.5-inches, and a thickness of about 0.125-inches.
  • Body 24 has a hollow interior 24 a (see FIGS. 3 and 4 ), and possesses an elongate, outside, diaphragm-contacting face 24 b (see FIGS.
  • Electrodes 26 , 28 present exposed, circular faces 26 a , 28 a , each having a diameter herein of about 0.15-inches.
  • these electrodes function, in an implanted-condition operation of system 20 , both to sense heart-related electrical activity—done in a so-called first, or one, mode of operation, and to apply controlled, asymptomatic, electrical stimulation to the diaphragm—done in a so-called second, or other, independent mode of operation.
  • capsule shape illustrated in FIGS. 1-4 , inclusive, and the several specific dimensions just mentioned, are not critical, and may be varied selectively according user wishes to suit different, particular implantation applications. What is important, of course, is that the shape and dimensions of capsule 24 be suitable and comfortable, and designed for minimally invasive placement for operational residence within a subject's anatomy. As will be explained below, while preferred placement involves, effectively, stabilized attachment to a surface region which is near the upper portion of a subject's diaphragm (inferior or superior), there may be other diaphragmatic locations that are suitable for placement.
  • a suitable, conventional, non-electrically-conductive, biocompatible mesh 30 (see FIGS. 1 and 2 ), is affixed to capsule face 24 b to facilitate, following system implantation, natural-process anatomical bonding, for positional stabilization, to a selected surface region (inferior or superior) in/on a subject's diaphragm. Inclusion of such a mesh is optional, but useful.
  • inferior surface-region placement on the diaphragm is preferred, and also preferably, though not necessarily, at a diaphragmatic location which is left-lateral in a subject's anatomy. Additionally, under all circumstances involving superior surface-region placement, such placement should be one where capsule 24 is out of direct contact with the heart.
  • system 20 housed within the hollow interior 24 a in capsule body 24 , are various electrical and mechanico-electrical, system-operational components, including an electrical circuit structure 32 which, through the included presence in it of logic-including, internal-control circuitry (still to be pointed out in the drawings), manages all system electrical-performance activity, a battery 34 which furnishes all needed operating power for the system, and a multi-axial (three-dimensional herein) accelerometer, or mechanical sensing structure, 36 which, with the system in an appropriate anatomically implanted condition, senses a variety of mechanical and sound activities, such as diaphragmatic-motion activities, and heart sounds.
  • an electrical circuit structure 32 which, through the included presence in it of logic-including, internal-control circuitry (still to be pointed out in the drawings), manages all system electrical-performance activity
  • a battery 34 which furnishes all needed operating power for the system
  • a multi-axial (three-dimensional herein) accelerometer, or mechanical sensing structure, 36 which, with the system in an appropriate anatomically implante
  • the accelerometer's sensing of diaphragmatic-motion activity a sensing capability enhanced by its proposed, and intended, implanted placement in what is referred to herein as a motion-sensing relationship directly on the diaphragm, it produces an important electrical, diaphragmatic-motion confirmation signal for delivery to electrical circuit structure 32 , which signal is directly indicative of the waveform of such motion.
  • This signal is significantly useful for assuring that actually applied electrical diaphragmatic stimulation is as best-suited as possible for triggering the desired biphasic diaphragmatic movement intended to maximize hemodynamic performance enhancement. This assuring comes about because, according to the methodology of the present invention, the waveform represented by the accelerometer's supplied confirmation signal is regularly compared with a reference waveform “known” to the system of the invention.
  • Heart sounds sensed by the included accelerometer are useful for many purposes, and especially the S1 heart sound which is used, in an already (above) mentioned, modified form of the invention to act, and be recognized as, a valid mechanical V-event in relation to which appropriate timing for the application of a diaphragmatic stimulation is measured.
  • accelerometer not directly related to the practice and methodology of the present invention, but nevertheless available, for example, to a physician monitoring various subject conditions that may, in different ways, have a relationship to hemodynamic performance, include subject activity levels, subject body posture, respiratory information, such as respiration rate, sleep-disordered breathing events, heart murmurs, and perhaps others.
  • circuit structure 32 An operative connection between circuit structure 32 and accelerometer 36 is represented in FIG. 5 by conductors 36 a , 36 b.
  • Electrodes 26 , 28 are operatively connected to circuit structure 32 for bimodal (sensing/stimulating) operation through what may be thought of as bi-directionally employed conductors 26 b , 28 b , respectively, and these electrodes, circuit structure 32 , battery 34 , and accelerometer 36 are all appropriately operatively interconnected to function collaboratively in manners shortly to be described.
  • Electrical circuit structure 32 features what is referred to as logic-including, internal-control circuitry, also referred to herein as computer structure, or more simply as a computer, 38 , possessing waveform monitoring and recording substructure 40 , and optionally (representationally present herein), timing adjustment substructure 42 .
  • computer 38 which could, if desired, be fully hard-wired to perform its intended functions, is herein incorporated and configured with a microprocessor, or the like, so as to be at least partially, if not fully, algorithmically software-programmable structure—programmable, in the system now being described, not only initially, but, if desired at later times, by close-proximity telemetry communication accommodated through a system-included, conventional, short-range radio 44 having an antenna 44 a .
  • Computer 38 also includes a suitable, conventionally designed “state machine” (not specifically, separately illustrated in the drawings) for implementing various important timing controls, as will be explained below herein.
  • FIG. 6A furnishes, as stated earlier, a frontal view of an internal portion 46 of a subject's anatomy illustrating, generally at 48 , preferred, implanted positioning therein proposed for the system 20 pictured in FIGS. 1-4 , inclusive.
  • system 20 is simply illustrated by a very evident, generally horizontally disposed, thickened, dark line, and specifically, what is illustrated, is that capsule 24 in this system is placed at a selected surface region 48 a on the inferior side of the subject's diaphragm 50 .
  • capsule 24 is positioned left-laterally in the subject's anatomy, clearly out of contact with the subject's heart 52 , and actually in a modest state of compression between the inferior side of diaphragm 50 and the subject's immediately underlying liver, seen generally, and fragmentarily only, at 54 .
  • capsule 24 is disposed with its electrode face 24 b (not specifically seen or marked in FIG. 6A ) facing the inferior surface of the diaphragm, with electrodes 26 , 28 (also not specifically seen in this figure) directly contacting diaphragmatic surface region 48 a.
  • capsule 24 has been implanted through conventional laparoscopy—a surgical practice which forms no part of the present invention.
  • FIG. 6B this figure also shows just-mentioned, internal, anatomical portion 46 , and is similar to FIG. 6A , except that it shows an alternative placement in the subject's anatomy for capsule 24 in system 20 .
  • capsule 24 has been placed on the superior surface of diaphragm 50 at an implantation position generally shown at 56 , and specifically on a selected, diaphragmatic surface region 56 a , which has a left-lateral disposition in the subject's anatomy similar to the left-lateral implantation disposition pictured on the underside of diaphragm 50 in FIG. 6A .
  • capsule 24 is disposed with its electrode face 24 b (not specifically seen or marked) facing the superior surface of the diaphragm, and with electrodes 26 , 28 (also not specifically shown in FIG. 6B ) directly in contact with the diaphragm.
  • the capsule In the disposition shown in FIG. 6B for capsule 24 , the capsule is slightly compressed between the superior surface of diaphragm 50 and the underside of the subject's left lung 58 .
  • this capsule has been implanted through conventional thoracotomy—another surgical procedure which also forms no part of the present invention.
  • FIGS. 8, 9A, 9B indicated generally at 60 in these three figures, and focusing attention initially here on what is shown in the FIG. 8 , is the second. above-mentioned, principal form of the invention, which is a self-powered, implantable, distributed form of the invention—distributed in the sense that it includes a pair of spaced component assemblies 62 , 64 , operatively interconnected by appropriate, elongate, communication lead structure 66 . Except for the fact that this form of the invention has the just-mentioned distributed nature, and the further fact that it's distributed componentry, when implanted in a subject's anatomy as pictured generally in FIGS.
  • 9A, 9B is uniquely associated with this distributed embodiment form, it includes all of the operatively interconnected electrical and mechanico-electrical componentry described above for system form 20 —interconnected as illustrated schematically in FIG. 5 . Additionally, the performance of system 60 is essentially identical to that of system 20 .
  • component assembly 62 includes a cylindrical housing 68 , from one side of which projects a spiral-form, diaphragm-attaching electrode 70 , and in which is appropriately mounted a three-dimensional accelerometer 72 represented by a small thickened and darkened line in FIG. 8 , and next to housing 68 , and represented by a small rectangle, another electrode 74 which, together with electrode 70 , form the previously mentioned bimodal electrodes.
  • electrodes 70 , 74 constitute the bimodal electrodes structure discussed above.
  • FIG. 8 Shown immediately to the right of component assembly 62 in FIG. 8 , and visually linked to the image of this component assembly by a curved, double-arrow-headed arrow 76 , is a symbolic representation 78 of assembly 62 , which symbolic representation is employed (as can be seen) in each of FIGS. 9A, 9B to enable a simpler way of picturing there the respective presences of assembly 62 in the anatomical images presented in these two figures.
  • Electrode 70 the spiral-form electrode, is designed to enable spiral, attachable embedment into the structure of a subject's diaphragm for securing component assembly 62 in place, and in a manner whereby both electrodes 70 , 74 will essentially be in contact with a selected surface region in the diaphragm, with accelerometer 72 in an appropriate motion-sensing relationship relative to, and effectively in contact with, the diaphragm.
  • Lead structure 66 includes conductors (not illustrated in specific detail) which are appropriately connected to electrodes 70 , 74 , and to accelerometer 72 , which conductors extend in the lead structure to component assembly 64 .
  • Component assembly 64 includes all of the system electrical circuitry, the system battery, and the system radio and antenna (not specifically pictured in FIG. 8 ), such as those, same elements illustrated in FIG. 5 .
  • the length of lead structure 66 is a matter of user choice, and will typically be chosen, of course, to accommodate intended implantation disposition of system 60 within a particular subject's anatomy.
  • FIGS. 9A and 9B Focusing now on FIGS. 9A and 9B , and beginning with what is shown in FIG. 9A , here, one can see that system 60 , as was true for the illustration provided in FIG. 6A for system 20 , is disposed at previously mentioned implantation position 48 on also previously mentioned inferior diaphragmatic surface region 50 a .
  • system 60 is disposed at previously mentioned implantation position 48 on also previously mentioned inferior diaphragmatic surface region 50 a .
  • component assembly 62 is shown in FIG. 9A , with lead structure 66 broken away, and component assembly 64 not specifically pictured. A reason for this is that what is important to note with respect to what is seen in FIG.
  • 9A is the diaphragmatic positioning of component assembly 62 , with one recognizing that implantation of the other end of system 60 , namely, component assembly 64 , can be located at the user's choice, and suitably, anywhere in the subject's anatomy below diaphragm 50 .
  • FIG. 9B which, as has already been mentioned, is very similar to FIG. 6B , shows system 60 disposed at previously mentioned implantation position 56 on also previously mentioned diaphragmatic surface region 50 b , located on the superior side of diaphragm 50 .
  • lead structure 66 is broken off with component assembly 64 omitted from FIG. 9B , one here recognizing that the installer of system 60 will choose an appropriate, above-the-diaphragm placement site for component assembly 64 .
  • FIGS. 6A, 6B, and 9A, 9B for systems 20 , 60 , respectively, which dispositions, are left-lateral in the subject's anatomy, and either inferior (preferred) or superior relative to the diaphragm, in each of these dispositions the electrodes and the accelerometers are essentially in direct contact with the described and illustrated surface regions in the diaphragm, out of direct contact with the heart. Additionally, in each of the system dispositions shown in these four figures, the electrodes in the respective systems are well positioned to detect easily heart-associated electrical activity, and the accelerometers are similarly positioned to detect easily heart sounds, and, of course, diaphragmatic movement/motion.
  • FIGS. 7A and 7B system components of the invention have been omitted so that one can more easily focus on the motion-created nature of, and behaviors associated with, diaphragmatic electrical stimulation produced by operations of the systems of the invention.
  • FIGS. 7A, 7B system components of the invention have been omitted so that one can more easily focus on the motion-created nature of, and behaviors associated with, diaphragmatic electrical stimulation produced by operations of the systems of the invention.
  • the anatomical left side of diaphragm 50 is shown in solid outline in a non-stimulated condition relative to the adjacent anatomical components, and particularly relative to heart 52 and its left ventricle.
  • FIG. 7B pictures relevant, moved relationships which exist immediately following the conditions shown in FIG. 7A . More specifically, an upwardly pointing arrow 82 in FIG. 7B shows conditions wherein diaphragm 50 has moved upwardly in a cranial direction to the exaggerated, moved position for it shown in dashed lines at 50 B—a diaphragmatic movement which drives upwardly on the underside of the left ventricle in the heart to create a heart and left ventricle moved condition pictured in dashed lines at 52 B.
  • the time-sequential moved conditions pictured in FIGS. 7A, 7B are, essentially, repeated synchronously in each cardiac cycle of a subject's heart in accordance with what constitutes herein predetermined timing associated with, and triggered by, the sensed occurrence of a valid, electrical or mechanical V-event, sensed either electrically by the bimodal electrode structure functioning in its “one”, sensing mode as established for it by operatively connected electrical circuit structure 32 , or mechanically by the included system accelerometer.
  • FIGS. 10 and 11 present conventional-style laddergrams which picture, respectively, what are referred to herein as (a) early, or anticipatory, diaphragmatic stimulation (PIDS), and (b) late, or following, diaphragmatic stimulation (PIDS).
  • PIDS diaphragmatic stimulation
  • FIGS. 12 and 13 present conventional-style laddergrams which picture, respectively, what are referred to herein as (a) early, or anticipatory, diaphragmatic stimulation (PIDS), and (b) late, or following, diaphragmatic stimulation (PIDS).
  • PIDS diaphragmatic stimulation
  • PIDS diaphragmatic stimulation
  • each figure includes a pair of vertically spaced, horizontal time lines, labeled “V” and “P”, where V stands for a V-event, and P stands, in a shortened manner, for the acronym PIDS (electrical diaphragmatic stimulation).
  • V stands for a V-event
  • P stands, in a shortened manner, for the acronym PIDS (electrical diaphragmatic stimulation).
  • the time lines in these two drawing figures effectively cover four, representative cardiac cycles, and each figure includes, at its lower left side, a self-explanatory, graphical-symbol legend which is associated with the several, and various, graphical indicia that are distributed along the time lines above in the figure.
  • V-PIDS timing periods or delays relate to what are referred to herein as V-PIDS timing periods or delays, and also as predetermined timed relationships—parameters that are functional in the operation of the system of the invention in accordance either with (a) user-selected presetting of these delays, (b) used re-setting of these delays after a period of system operation, and/or (c) on-the-fly, system-internal, systemically self-effected adjustments of such delays, where such system-internal adjustments are permitted (i.e., user-selectively accommodated by appropriately system-included, conventional logic programming).
  • V-PIDS delay parameter both in a necessary pre-setting manner with the system in an implanted (or not) condition, and later, if desired, in a system-implanted re-setting situation, are permitted via remote telemetry, or otherwise.
  • the graphically illustrated V-PIDS delays “represented” by the sloping, dashed lines in FIGS. 10 and 11 are actually measureable, i.e. visualizable, graphically in these figures in a manner and direction which is horizontally parallel to the time lines, and not angularly.
  • V-events have been selected to be the markers, i.e., the triggers, for PIDS stimulation.
  • FIGS. 10 and 11 there are two, important, and importantly related, timing periods that are taken into account in the practice of the present invention, one of which, the V-PIDS delay period, has just been discussed, and the other of which is the length of the so-called refractory period that exists in each of a subject's cardiac cycles, immediately following a sensed, valid V-event in that cycle.
  • the relevant refractory periods are represented graphically by elongate, vertically-thin, horizontal rectangles distributed along the time lines.
  • the graphical legends presented in FIGS. 10 and 11 make clear which illustrated “rectangles” these are.
  • Timing operations with respect to these two time periods are under the control of two, logic-based timers that are realized/implemented, and “operated”, so-to-speak, in appropriate timing-tracking manners by the previously-mentioned, included-logic state machine in its association with the electrical-circuitry-included logic, or computer, structure.
  • the time-period associated with the timer which deals with tracking a cardiac-cycle refractory period, a period which, as was just mentioned, begins immediately following the sensing of a chosen, valid V-event, involves subject-specific data that is pre-known, for example, to a medical practitioner using the system of the invention, and who is familiar with the particular subject to be equipped with the system.
  • subject-specific data that is pre-known, for example, to a medical practitioner using the system of the invention, and who is familiar with the particular subject to be equipped with the system.
  • two pieces of subject-specific information are relevant to establishing what will be, at least initially, a preset duration for a timed refractory period.
  • FIG. 10 in the two-drawing-figure, pictorial-numeric sequence which has been selected for the presentations in the drawings of FIGS. 10 and 11 , has been chosen to illustrate such stimulation.
  • V-PIDS timing delay “represented” in FIG. 10 by the previously-mentioned, sloping dashed lines, is calculated by performing, effectively, a subtraction, from the then-available averaged timing determined between successive, valid V-events, of the brief, precursor interval (just mentioned above) the beginning of which is intended to define the moment of triggering of a PIDS stimulation in anticipation of the expected, very shortly following, next-valid, and sensed, V-event.
  • system of the present invention may be structured in a conventional manner to allow the making of a change associated with early PIDS stimulation through the making of a change in settings available to the system describing, differently, the short precursor (subtraction anticipatory) interval just discussed.
  • this figure illustrates the potential problem-creating possibility (mentioned earlier) of an errant V-event which occurs, outside of normal cardiac behavior, within a particular cardiac cycle's refractory period.
  • a presentation of the occurrence of such an errant V-event which has taken place during the illustrated cycle's refractory period is presented to the right of this indication in the upper time line, and specifically below the associated, lower time line.
  • text is presented indicating that there is not to be an immediately-next-following PIDS stimulation—a protective measure, as noted earlier.
  • FIG. 11 describes what has been referred to as a late PIDS stimulation situation. This situation is very easy to understand, in the sense that to implement it, all that is required is a system setting for a predetermined V-PIDS delay time which is very short, typically, and which, within a common cardiac cycle, shortly follows a sensed, valid V-event.
  • small blackened rectangles distributed, as shown, along the V time lines in these figures mark short, conventionally-system-implemented blanking periods that are created and exist to prevent a stimulation pulse from producing unintended cardiac electrical activity.
  • these blanking periods fall outside of the cardiac-cycle refractory periods.
  • they occur during refractory periods.
  • FIG. 12 illustrates, along two, vertically spaced, time-related time lines, (1) an upper graphical trace of an ECG waveform received from subject-implanted system electrodes, picturing a large plurality of successive subject cardiac cycles, including the evident presences of cycle-synchronized PIDS stimulations, and (2) a lower graphical trace of related output information received from the implanted-system-included accelerometer showing both the lower-frequency characteristic of normal respiration, and the superimposed, higher-frequency, cardiac-cycle-synchronized, biphasic diaphragmatic motions that have resulted from the PIDS stimulations shown above in the electrically illustrated cardiac cycles.
  • the waveforms of these biphasic diaphragmatic motions, captured and recorded, as they are, for later reporting by the system of the present invention, are importantly useful for helping a medical professional, in the setting of actually seeing the waveform of what biphasic, diaphragmatic, stimulation-produced motion looks like, to assess both, ultimately, the quality of a subject's hemodynamic performance, and also the quality of enhancement-assistance thereof furnished by the invention.
  • FIG. 13 furnishes an enlarged, and time-stretched, view of fragments of the two traces presented in FIG. 12 , selected from the region in FIG. 12 marked by the two, vertical, laterally-spaced dashed lines that mark a display region for FIG. 13 designated 84 in FIG. 12 .
  • each illustrated PIDS stimulation which is short-term and pulse-like in nature, produces, in the represented subject's diaphragm's movement, a related, cardiac-cycle-synchronized, relatively high frequency, biphasic, caudal-followed-by-cranial movement of the diaphragm.
  • An important and special feature of the present invention involves the capturing and recording of accelerometer data associated with the nature of actual, stimulation-produced diaphragmatic biphasic movement.
  • This capture and recording in association with an importantly implemented, and uniquely contemplated, comparison of captured, actual diaphragmatic motion waveforms with a system-stored, carefully chosen, reference waveform, yields reportable information that allows a system user to initiate stimulation adjustments to improve matters.
  • This comparison activity produces system-stored comparison data which is retrievable by telemetry to furnish valuable confirmatory evidence of the viability of the implemented diaphragmatic stimulation respecting the maximizing and achieving of hemodynamic performance.
  • FIG. 14 illustrates, in block/schematic form, both the basic, and a modified, form of the architecture of the methodology of the present invention.
  • the “overall” archaeology, as shown in FIG. 14 is illustrated generally at 86 . It includes, as steps represented in block form, six different blocks, including block 88 (Sensing), block 90 (Applying), block 92 (Monitoring), block 94 (Comparing), block 96 (Recording), and block 98 (Choosing).
  • Blocks 88 - 96 inclusive, are drawn each with a solid-line outline to signify that they describe, effectively, the basic, or core, methodology of the invention.
  • Block 98 which is outlined with a dashed line, represents one modified form of the invented methodology. Reading from left to right in FIG. 14 , the several blocks there pictured are connected in the order of associated behaviors, with arrow-headed, right-pointing lines connecting these blocks, as shown, to symbolize, the flow of methodologic activity.
  • the present invention thus offers a method for improving the hemodynamic performance of a subject's heart including, from adjacent a selected surface region in the subject's diaphragm which is out of contact with the heart, (1) Sensing and noting (Block 88 ) the presences in the subject's cardiac cycles of a selected one of (a) per-cycle valid electrical, and (b) per-cycle valid mechanical, V-events, (2) based upon such sensing, and upon noting each of such selected, V-event presences, Applying (Block 90 ), in a predetermined timed relationship to such a noting, associated, asymptomatic electrical stimulation directly to the diaphragm, preferably at the selected diaphragmatic surface region, for the purpose of triggering biphasic, caudal-followed-by-cranial motion of the diaphragm, (3) following the applying step, Monitoring (Block 92 ) the waveform of resulting diaphragmatic motion, (4) after performing the monitoring step, Comparing (Block
  • the invention methodology in a modified form, further includes (1) Choosing (Block 98 ) the selected diaphragmatic surface region to be on one of (a) the inferior, and (b) the superior, side of the diaphragm, and (2) choosing the selected, per-cycle valid V-event whereby, if it is to be electrical, it is one of (a) the R wave, and (b) the Q wave, and if mechanical, it is the S1 heart sound.
  • timing interval to pre-assign to the refractory period timer operated by the state machine, and this timing interval will be based upon subject-specific information drawn from pre-knowledge about the subject's expected likely heart-rate range, and typical refractory period time length beginning with the onset of the R wave, and ending with the end of that refractory period.
  • the system is implanted appropriately, as illustrated in FIG. 6A , and is switched into operation, with the system user immediately collecting appropriate data to assess needed adjustment, from zero, to establish in the state machine the most appropriate early-PIDS time interval now to be “reset” for per-cycle calculation of the important V-PIDS delay period.
  • the system user immediately collects appropriate data to assess needed adjustment, from zero, to establish in the state machine the most appropriate early-PIDS time interval now to be “reset” for per-cycle calculation of the important V-PIDS delay period.
  • V-PIDS delay period thus set, the system of the invention now simply regularly estimates, through the on-the-fly averaging technique described above, a proper point in time, following the sensing in one cardiac cycle of a valid electrical V-event, to apply diaphragmatic stimulation in the following cardiac cycle appropriately, and shortly, before the next-sensed, valid electrical V-event. Errant electrical V-events sensed during a cardiac cycle's refractory period will not be used to trigger stimulation.
  • Each sensed, valid electrical V-event will result in asymptomatic electrical stimulation of the subject's diaphragm to produce high-frequency, biphasic, caudal-followed-by-cranial diaphragmatic movement, and this cycle-by-cycle activity will synchronously drive the left ventricle of the subject's heart in a biphasic, pumping-assist manner which will enhance hemodynamic performance as described above.
  • the system accelerometer will accurately follow the stimulation-induced biphasic diaphragmatic movement which is associated with each diaphragmatic stimulation, and will, cycle-by-cycle, communicate to the electrical circuit structure the mentioned, related, diaphragmatic-motion confirmation signal whose associated waveform will be compared with that of the mentioned, carefully-chosen reference waveform to generate, for storage and later retrieval, cardiac-cycle-by-cardiac-cycle waveform comparison data.

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US14/107,976 US9498625B2 (en) 2012-12-19 2013-12-16 Hemodynamic performance enhancement through asymptomatic diaphragm stimulation
US15/273,643 US9694185B2 (en) 2012-12-19 2016-09-22 Hemodynamic performance enhancement through asymptomatic diaphragm stimulation
US15/288,130 US10335592B2 (en) 2012-12-19 2016-10-07 Systems, devices, and methods for improving hemodynamic performance through asymptomatic diaphragm stimulation
US15/612,690 US9968786B2 (en) 2012-12-19 2017-06-02 Hemodynamic performance enhancement through asymptomatic diaphragm stimulation
US15/950,774 US10315035B2 (en) 2012-12-19 2018-04-11 Hemodynamic performance enhancement through asymptomatic diaphragm stimulation
US16/395,970 US11020596B2 (en) 2012-12-19 2019-04-26 Hemodynamic performance enhancement through asymptomatic diaphragm stimulation
US16/399,896 US11147968B2 (en) 2012-12-19 2019-04-30 Systems, devices, and methods for improving hemodynamic performance through asymptomatic diaphragm stimulation
US17/243,341 US11684783B2 (en) 2012-12-19 2021-04-28 Hemodynamic performance enhancement through asymptomatic diaphragm stimulation
US17/477,432 US11666757B2 (en) 2012-12-19 2021-09-16 Systems, devices, and methods for improving hemodynamic performance through asymptomatic diaphragm stimulation
US18/137,982 US12364859B2 (en) 2012-12-19 2023-04-21 Systems, devices, and methods for improving hemodynamic performance through asymptomatic diaphragm stimulation
US18/196,148 US12144993B2 (en) 2012-12-19 2023-05-11 Hemodynamic performance enhancement through asymptomatic diaphragm stimulation

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US20210244947A1 (en) 2021-08-12
EP2934668B1 (en) 2018-08-22
US9694185B2 (en) 2017-07-04
JP6285956B2 (ja) 2018-02-28
US9968786B2 (en) 2018-05-15
US20180229034A1 (en) 2018-08-16
US20230277855A1 (en) 2023-09-07
WO2014099820A1 (en) 2014-06-26
US11020596B2 (en) 2021-06-01
US12144993B2 (en) 2024-11-19
JP2016501108A (ja) 2016-01-18
CN104994906B (zh) 2017-05-24
US20190247656A1 (en) 2019-08-15
US20140172040A1 (en) 2014-06-19
CN104994906A (zh) 2015-10-21
US20170266444A1 (en) 2017-09-21
US11684783B2 (en) 2023-06-27
US20170007832A1 (en) 2017-01-12
US10315035B2 (en) 2019-06-11
EP2934668A1 (en) 2015-10-28

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